US 8168159 B2
The present invention discloses a method for the enzyme-mediated, site-specific, in-vivo precipitation of a water soluble molecule in an animal. The enzyme is either unique to tumor cells, or is produced within a specific site (e.g., tumor) at concentrations that are higher than that in normal tissues. Alternatively, the enzyme is conjugated to a targeting moiety such as an antibody or a receptor-binding molecule.
1. A compound represented by the formula:
R1 is selected from the group consisting of a hydrogen radical, a radionuclide, a moiety labeled with one or more radionuclides, a boron atom, a moiety labeled with one or more boron atoms, and a boron cage;
R2 is selected from the group consisting of a hydrogen radical, a radionuclide, and a boron cage;
at least one of R1 and R2 is not a hydrogen radical; and
R3 is a prosthetic group that can be cleaved by a hydrolytic enzyme.
2. The compound of
3. The compound of
4. The compound of
5. The compound of
6. The compound of
This application is a continuation of U.S. patent application Ser. No. 09/839,779, filed Apr. 20, 2001, now U.S. Pat. No. 7,514,067, which claims the benefit of priority to U.S. Provisional Patent Application Ser. No. 60/199,350, filed Apr. 25, 2000. The entire teachings of each of these applications are incorporated herein by reference.
Monoclonal antibodies (MAb), by virtue of their unique in-vitro specificity and high affinity for their antigen, have generally been considered particularly attractive as selective carriers of cancer radiodiagnostic/therapeutic agents. Several reasons underlie these expectations: (i) they show a high degree of specificity and affinity for their intended target; (ii) they are generally nontoxic; and (iii) they can transport such agents. The application of MAb in animals and humans for both tumor scintigraphic detection (labeled with 123I, 131I, 93mTc, and 111In) and therapy (labeled with the beta emitters 131I, 186Re, 90Y, 165Dy, 67Cu, and 109Pd; the alpha emitters 211At, 212Bi, and 213Bi; or conjugated to various toxins and cytotoxic drugs) is the focus of work in many research laboratories.
In pursuing these studies, the basic assumption continues to be that MAb have a role in the radioimmunodiagnosis and radioimmunotherapy of cancer. However, while most published work on this subject has demonstrated their utility in the diagnosis and treatment of various tumors in experimental animal models, the use of radiolabeled MAb to target and treat solid tumors in cancer patients has been for the most part unsuccessful. There are at least five reasons for the results seen in humans:
1. Low tumor uptake. Thus far, most studies in humans have demonstrated that the percentage injected dose per gram of tumor (% ID/g) is extremely low. As a result, the absolute amount of the therapeutic radionuclide within the tumor is much less than that needed to deposit a radiation dose sufficiently high to sterilize the tumor.
2. High activity in the whole body. A corollary to low tumor uptake is the presence of ˜90%-99% of the injected radiolabeled MAb in the rest of the body. This has led to the deposition of high doses in normal tissues and unacceptable side effects, and a reduction in the maximum tolerated dose (MTD).
3. Slow blood clearance. In most human radioimmunotherapy trials, whole MAb (MW˜150,000 Da) have been used. The clearance of such high-molecular-weight proteins from blood and nontargeted tissues is rather slow. The resulting systemic exposure to the radioisotope thus produces high doses to the bone marrow and a lowering of the MTD.
4. Limited intratumoral diffusion. The high molecular weight of MAb also limits their ability to extravasate and diffuse through the tumor mass. As a consequence, many areas within the tumor are spared from receiving a lethal dose of radiation (i.e., the areas are either outside the range of the emitted particle or receive a sublethal dose).
5. Heterogeneity of tumor-associated antigen expression. Many studies have demonstrated that a substantial proportion of the cells within a tumor mass show reduced/no expression of the targeted antigen. This also will lead to nonuniform distribution of the radionuclide within the tumor mass and the sparing of a large number of cells within the tumor.
In an attempt to bypass some of the limitations of these unique molecules, various two-step and three-step approaches have been theorized, in which a noninternalizing antitumor antibody is injected prior to the administration of a low-molecular-weight therapeutic molecule that has an affinity/reactivity with the preinjected antibody molecule. These systems can be categorized into two major classes: MAb-directed enzyme prodrug therapy and MAb-directed radioligand targeting, details of which are known in the art.
It is clear that under ideal conditions, a radiolabeled therapeutic agent must meet the following requirements: (i) be labeled with an energetic particle emitter, (ii) be taken up rapidly and efficiently by the tumor, (iii) be retained by the tumor (i.e. very long effective clearance half-life), (iv) have a short residence within normal tissues (i.e., short effective half-life in blood, bone marrow, and whole body), (v) achieve high tumor-to-normal tissue uptake ratios, (vi) attain an intratumoral distribution that is sufficiently uniform to match the range of the emitted particles (i.e. all tumor cells are within the range of the emitted particles), and (vii) achieve an intratumoral concentration that is sufficiently high to deposit a tumoricidal dose in every cell that is within the range of the emitted particle.
The present invention relates to a method for the enzyme-mediated, site-specific, in-vivo precipitation of a water soluble molecule in an animal. The enzyme is either unique to tumor cells (i.e. only produced by tumor cells), or is produced within the specific site (e.g., tumor) at concentrations that are higher than that in normal tissues. Alternatively, the enzyme is conjugated to a targeting moiety such as an antibody. For example, an antibody-enzyme conjugate is injected into tumor bearing animals and following tumor targeting and clearance from normal tissues and organs, the water soluble substrate is injected. Owing to the negatively charged prosthetic group (e.g. phosphate) present within its molecules, the substrate is highly hydrophilic, is not internalized by mammalian cells, and should clear from circulation at a rate that is compatible with its physical characteristics (e.g. molecular weight, charge). However, being a substrate for the enzyme (pre-targeted or otherwise), this water soluble molecule loses the prosthetic group and the resulting molecule precipitates out due to its highly water-insoluble nature. The precipitated molecule is thus “indefinitely trapped” within the targeted tissue. In one of its aspects (Enzymatic Radiolabel Insolubilization Therapy, ERIT), the substrate is radiolabeled with a gamma or a positron emitting radionuclide and as such, the location of the precipitate can be detected by external imaging means (SPECT/PET). On the other hand, when the radionuclide is an alpha or a beta particle emitter, the trapped precipitated radioactive molecule will maintain the radionuclide within the targeted tumor thereby enhancing its residence time and delivering a high radiation dose specifically to the tumor relative to the rest of the body. In yet another aspect (Enzymatic Boron Insolubilization Therapy, EBIT), the substrate is conjugated to one/more boron-containing molecule and upon precipitation within its intended target, the tumor is subjected to epithermal neutrons with the subsequent alpha particle emissions (Boron Capture Therapy).
In its simplest form, therefore, the present invention is based on the conversion of a chemical (e.g. quinazolinones, benzoxazoles, benzimidazoles, benzothiazoles, indoles, and derivatives thereof) from a freely water-soluble form to a highly water-insoluble form and hence in vivo precipitation at the specific site where an enzyme (e.g. acetylglucosaminidases, acetylneuraminidases, aldolases, amidotranferases, arabinopayranosidases, carboxykinases, cellulases, deaminases, decarboxylases, dehydratases, dehydrogenase, DNAses, endonucleases, epimerases, esterases, exonucleases, fucosidases, galactosidases, glucokinases, glucosidases, glutaminases, glutathionases, guanidinobenzodases, glucoronidases, hexokinases, iduronidases, kinases, lactases, mannosidases, nitrophenylphosphatases, peptidases, peroxidases, phosphatases, phosphotransferases, proteases, reductases, RNAses, sulfatases, telomerases, transaminases, transcarbamylases, transferases, xylosidases, uricases, urokinasess) or any other species capable of carrying out such a conversion in high concentrations. Pretargeting of enzyme or its equivalent species may be achieved by making use of specific antibodies or any such specific receptor-binding ligand to the desired sites in vivo. Note that the ligand may also be a peptide or hormone, with the receptor specific to the peptide or hormone.
Alternatively, the enzyme may be produced within the tumor site by the tumor cells themselves or following gene therapy or similar means. The chemical to be injected in the second step contains any nuclide suitable for imaging and/or therapy (e.g. Boron-10, Carbon-11, Nitrogen 13, Oxygen-15, Fluorine-18, Phosphorous-32, Phosphorous-33, Technetium-99m, Indium-111, Yttrium-90, Iodine-123, Iodine-124, Iodine-131, Astatine-211, Bismuth-212, etc.).
The accompanying drawings illustrate preferred embodiments of the invention as well as other information pertinent to the disclosure, in which:
This invention describes a novel approach that serves to localize water-insoluble, radioactive molecules within the extracellular (interstitial) space of a tumor. In one embodiment of this invention, a noninternalizing monoclonal antibody (MAb) to a “tumor-specific” antigen is chemically conjugated to the enzyme alkaline phosphatase (ALP); the MAb-ALP conjugate is administered intravenously (i.v.) to tumor-bearing animals, and after MAb-ALP tumor localization and clearance from circulation (high tumor to normal tissue ratios), a water-soluble, radiolabeled prodrug (PD) that is a substrate for ALP is injected intravenously. The conjugate or prodrug may also be injected intra-arterially, subcutaneously, into the lymphatic circulation, intraperitoneally, intrathecally, intratumorally, intravesically, or is given orally.
The prodrug substrate is represented by the following formula:
wherein BLOCK is a blocking group that can be cleaved from the remainder of the substrate by action of an enzyme, resulting in a water-insoluble drug molecule represented by the following formula:
wherein D contains a minimum of 2 linked aromatic rings, and R1 is a radioactive atom, a molecule labeled with one or more radioactive atom(s), a boron atom, or a molecule labeled with one or more boron atoms.
The radiolabel is selected from the group consisting of a gamma emitting radionuclide suitable for gamma camera imaging, a positron emitting radionuclide suitable for positron emission tomography, and an alpha or a beta particle emitting radionuclide suitable for therapy. The alpha particle emitting radionuclide may be, e.g., astatine-211, bismuth-212, or bismuth-213. The beta particle emitting radionuclide emits beta particles whose energies are greater than about 1 keV. The beta particle emitting radionuclide may be, e.g., iodine-131, copper-67, samarium-153, gold-198, palladium-109, rhenium-186, rhenium-188, dysprosium-165, strontium-89, phosphorous-32, phosphorous-33, or yttrium-90. Note also that the boron atom is suitable for neutron activation.
The BLOCK is selected from the group consisting of:
a monovalent blocking group derivable by removal of one hydroxyl from a phosphoric acid group, a sulfuric acid group, or a biologically compatible salt thereof;
a monovalent blocking group derivable by removal of a hydroxyl from an alcohol or an aliphatic carboxyl, an aromatic carboxyl, an amino acid carboxyl, or a peptide carboxyl; and a monovalent moiety derived by the removal of the anomeric hydroxyl group from a mono- or polysaccharide.
As the PD molecules percolate through the tumor mass, they will be hydrolyzed by the ALP molecules present within the tumor (MAb-ALP). The hydrolysis of PD (Compound 1, or Compound A below) leads to the formation of a water-insoluble, radiolabeled precipitate (D). It is anticipated that D (Compound 2, or Compound B below), as a consequence of its physical properties, will be trapped within the extracellular space of the tumor mass. Thus, when labeled with iodine-131 (131I), a radionuclide that decays by the emission of both a beta particle (Emax=610 keV; mean range=467 μm; maximum range=2.4 mm) and photons suitable for external imaging, the entrapped 131I-labeled D molecules will serve as a means for both assessing tumor-associated radioactivity (planar/SPECT) and delivering a protracted and effective therapeutic dose to the tumor.
Enzymatic hydrolysis of radiolabeled quinzalinone prodrugs
Radiolabeled 2-(2′-hydroxyphenyl)-4-(3H)-quinazolinone dyes are employed in the method of the present invention: These classes of compounds contain a hydroxyl group that forms an intramolecular six-membered stable hydrogen bond with the ring nitrogen and hence they are highly water-insoluble in nature. However, addition of a prosthetic group (e.g. phosphate, sulfate, sugars such as galactose or peptide) on the hydroxy group renders the molecule freely water-soluble. Furthermore, the presence of such prosthetic groups makes cell-membranes impermeable to these molecules; they are anticipated to have relatively short biological half-lives in the blood. However, when acted on by the enzyme, the prosthetic group is lost, resulting in the restoration of intramolecular hydrogen bonding, and the molecule becomes water-insoluble and precipitates.
The procedure for the synthesis of the unsubstituted quinazolinone dye (1, below), is as follows:
In order to make use of the above chemistry for the synthesis of radiolabeled quinazolinones, halogen substituted anthranilamides that are easily converted to the tin precursors needed for the exchange labeling with radiohalogens were used. Thus, for the synthesis of 5-haloanthranilamides (9) from 5-haloanthranillic acids (7), isatoic anhydrides were used, as shown below.
Synthesis of 5-halo-anthranilamides from 5-halo-anthranilic acids
2-Amino-5-iodobenzoic acid (10) and triphosgene were then dissolved in dry THF and the reaction mixture stirred at room temperature for 1 hour. An off-white precipitate formed and TLC showed that compound 10 is consumed, as shown below. The precipitate was filtered, washed with cold methanol, and crystallized in acetonitrile. 1H NMR indicated that the spectrum was an iodoisotoic anhydride (11).
A solution of iodoisotoic anhydride (11) was then suspended in THF and cooled in an ice-bath. Aqueous ammonium hydroxide was added dropwise, the reaction mixture was stirred for 15 minutes at 0° C. and 30 minutes at RT, and the solvent was evaporated. The white solid obtained was characterized by 1H NMR and identified as an iodoanthranilamide (12).
Next, Iodoanthranilamide (12) and salicylaldehyde were suspended in methanol and refluxed in the presence of catalytic amounts of p-toluene sulfonic acid (TsOH) for 30 minutes. To the pale-yellow precipitate (13) formed, 2,3-dichloro-5,6-dicyano-1,4-benzoquinone was added and the suspension was refluxed for 1 hour. The solid product was filtered, washed with cold methanol, characterized by 1H NMR, and identified as 2-(2′-Hydroxyphenyl)-6-iodo-4-(3H)-quinazolinone.
Synthesis of Ammonium 2-(2′-Phosphoryloxyphenyl)-6-iodo-4-(3H)-quinazolinone (15).
In one method, 2-(2′-Hydroxy)-6-iodo-4-(3H)-quinazolinone (14) was added to dried pyridine at 0° C., followed by phosphorus oxychloride. Silica gel TLC indicated that the reaction was completed within 2 min. The reaction solution was neutralized to pH 7.0 by the addition of ammonium hydroxide. The solvent was evaporated and the solid product was suspended in water, filtered, and purified by chromatography. Following elution (stepwise gradient: water followed by acetonitrile-water, 2:1), a yellow solution containing UV-visible product was collected, the solvent was evaporated, and the product was characterized by 1H and 31P NMR and identified as compound 15.
In an alternative method, ammonium 2-(2′-phosphoryloxyphenyl)-6-tributylstannyl-4-(3H)-quinazolinone (17) was dissolved in methanol, and sodium iodide was added followed by hydrogen peroxide. A yellow precipitate formed immediately. The reaction vial was vortex-mixed and incubated for 30 minutes at 37° C. Reversed-phase silica gel TLC showed approximately 50% conversion (solvent: acetonitrile-water, 1:1). The solvent was evaporated and the product purified by chromatography. TLC (solvent: chloroform-methanol, 1:1) showed the same Rf value (0.6), and proton and 31P NMR gave the same spectra as were obtained with the known compound 15 synthesized by the route shown above.
Synthesis of compounds 18 and 15 by iododestannylation
Next, to a dioxane solution containing 14, hexa-n-butylditin and tetrakis (triphenylphosphine) palladium were added, as shown above. The reaction mixture was refluxed for 1.5 hours and progress of the reaction was followed by silica gel TLC (solvent: methylene chloride-ethyl acetate, 9:1) to test for the formation of a more nonpolar product. The solvent was evaporated, and the crude yellow solid was purified on a silica gel column (stepwise gradient: starting with hexane followed by hexane-dichloromethane, 1:1). Following solvent evaporation, a yellow fluorescent solid 2-(2′-Hydroxy)-6-tributylstannyl-4-(3H)-quinazolinone 16 was obtained as identified by 1H NMR.
Next, to a stirred solution of 16 in dry pyridine cooled to 0° C., phosphorus oxychloride was added dropwise. The reaction mixture was stirred for 10 min at 0° C. and then quenched by the addition of ammonium hydroxide (Scheme 5). The solvent was evaporated, the crude product redissolved in methanol-acetate (1:1) and purified on a C18 column (stepwise gradient: water followed by acetonitrile-water going from 30% to 50% acetonitrile). The solvent was evaporated and the nonfluorescent solid Ammonium 2-(2′-Phosphoryloxyphenyl) 6-tributylstannyl-4-(3H)-quinazolinone 17 was obtained as identified by 31P NMR.
Next, three Iodo-beads were placed in a reaction vial, followed by 20 μl of 1 μg/μl solution of 17, 30 μl 0.1 M borate buffer (pH=8.3), and Na125I (800 μCi/8 μl of 0.1 M sodium hydroxide). After 20 minutes at room temperature, the crude reaction mixture was loaded on a Sep-Pak Plus C18 cartridge and eluted with 1 ml water and then 2 ml 10% acetonitrile in water. The product 18 was eluted with 20% acetonitrile in water (yield: ˜370 μCi; radiochemical yield: 46%). The radiolabeled product, co-spotted with nonradioactive compound 15 on reversed-phase TLC, showed a single spot on autoradiograph (solvent: acetonitrile-water, 1.5:2). Radiolabeled (151I) Ammonium 2-(2′-Phosphoryloxyphenyl)-6-iodo-4-(3H)-quinazolinone 18 co-injected with 15 into the HPLC showed a single radioactive peak (Rf=14 min) which matched the Rf value of 15.
X-Gal (5-bromo-4-chloro-3-indolyl β-D-galactose) is routinely used for the identification of lac+ bacterial colonies. The underlying principle is that the colorless X-gal which is freely water-soluble is converted to dark blue colored precipitate upon reaction with b-galactosidase enzyme.
When the prodrug ((1) or Compound A), a non-fluorescent, stable, water-soluble compound, is incubated (37° C.) with alkaline phosphatase (ALP), a bright yellow-green fluorescent, clearly visible precipitate is formed whose Rf on thin layer chromatography (TLC) corresponds to drug ((2) or Compound B). In order to assess the kinetics of this enzyme-based hydrolysis (i.e. conversion of Compound A to Compound B) at 37° C., Compound A (60 μM) was mixed with 10 units ALP in 0.1 M Tris (pH 7.2) and the reaction kinetics followed over time using a Perkin-Elmer LS50B Luminescence Spectrometer with excitation at 340 nm and emission at 500 nm. There is a rapid increase in fluorescence intensity under these experimental conditions, as shown in
In order to further characterize the 125I-labeled prodrug, 125I-labeled Compound A (˜10 μCi/100 μl 0.1 M Tris buffer, pH 7.2) was incubated with 5 units ALP or heat-inactivated (70° C., 2 hours) ALP; the samples were spotted on reversed-phase TLC plates that were then run in acetonitrile-water (1.5:2). Autoradiography demonstrates the complete conversion of 125I-labeled Compound A to 125I-labeled Compound B only in the presence of the active enzyme, as shown in
In order to determine blood clearance of AP125IQ, mice (n=5/group) were injected i.v. with the radioiodinated prodrug and bled over a 1 hour period, the radioactive content per gram of blood was measured, and the percentage injected dose per gram (% ID/g) calculated. The results as shown in
In order to assess the chemical nature of the radioactivity in blood (i.e. determine stability of 125I-labeled Compound A in blood), ethanol was added to the blood samples (collected during the first 40 min), the tubes were centrifuged, and the supernatant was spotted on TLC. The plates were run in acetonitrile-water (1.5:2) and autoradiographed. The results show (i) the presence of a single spot whose Rf is the same as that observed with 127I-labeled Compound A, and (ii) no evidence of free iodine. These data demonstrate the stability of 1-labeled Compound A in serum.
The biodistribution of 125I-labeled Compound A in normal tissues was also considered. Mice (n=30) were injected i.v. with the radiopharmaceutical (˜5 μCi/100 μl), the animals were killed at 1 hour (n=15) and 24 hours (n=15), and the radioactivity associated with blood, tissues, and organs was determined. As shown in
The biodistribution of 125I-labeled Compound B was also examined in various tissues in normal mice. In these experiments, 125I-labeled Compound A was synthesized, purified, and incubated at 37° C. in the presence of ALP overnight. TLC demonstrated the complete conversion of 125I-labeled Compound A to 125I-labeled Compound B. Mice (n=10) were injected i.v. with 125I-labeled Compound B (˜5 μCi/100 μl) and killed (n=5) at 1 hour and 24 hours. The 1 hour data, as shown in
In order to demonstrate within an animal the conversion of the water-soluble 125I-labeled Compound A to the water-insoluble 125I-labeled Compound B, ALP was dissolved in saline (50, 100, 150, 200, 250, 300, 400 units/10 μl) and using a 10 μl syringe, 10 μl enzyme preparation was injected s.c. in the forelimb of Swiss Alpine mice. Five-minutes later, 20 μCi 125I-labeled Compound A was injected i.v. (tail vein). The animals were killed 1 hour later and the radioactivity in the forelimbs was measured. The results, as shown in
In order to demonstrate that once formed, the water-insoluble Compound B is retained “indefinitely” within the tissue where it is formed, 125I-labeled Compound B was dissolved in 100 μl DMSO (under these conditions, 125I-labeled Compound B is completely soluble in DMSO; however, when 100 μl water are added, a visible precipitate forms immediately that contains 125I-labeled Compound B radioactivity). Five μl of this solution was injected s.c. into the right forelimb of mice (n=15), followed by 5 μl saline. For comparison, 125I-labeled Compound A (5 μCi/5 μl saline) was injected s.c. into the left forelimb of the same mice and followed with 5 μl DMSO. The animals were killed after 1 hour, 24 hours, and 48 hours, the radioactivity associated with the forelimbs was measured, and the percentage of radioactivity remaining was calculated (at the 24 hour time point, the biodistribution of radioactivity in various tissues and organs was also determined). The data (
While this invention has been described in terms of exemplary embodiments, it is not limited thereto. Rather, the appended claims should be construed broadly to include other variants and embodiments of the invention which may be made by those skilled in the art without departing from the scope and range of equivalents of the invention.